Curable material delivery device with a rotatable supply section

ABSTRACT

An apparatus and method for introducing material into an injection site of a patient is disclosed. The device includes a cannula and a carrier. The cannula is inserted into an injection site of a patient. The carrier is connected to an injector containing a volume of material. Material may be pre-loaded into the carrier so that the material is delivered to a distal end of the carrier from the injector and the carrier is thus pre-loaded with material. A portion of the distal end of the pre-loaded carrier is inserted into the cannula and material is delivered to an injection site. The supply section can be rotatable with respect to the longitudinal axis of the inner section.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 11/526,164, entitled “Curable Material Delivery Device With Rotatable Supply Section,” filed Sep. 22, 2006, which is a continuation-in-part of U.S. patent application Ser. No. 11/359,184, entitled “Curable Material Delivery Device,” filed Feb. 22, 2006.

TECHNICAL FIELD

The present invention relates to devices and methods for stabilizing bone structures. More particularly, it relates to devices, systems and methods for delivering a curable, stabilizing material into a bone structure.

BACKGROUND INFORMATION

Surgical intervention at damaged or compromised bone sites has proven highly beneficial for patients, for example patients with back pain associated with vertebral damage.

Bones of the human skeletal system include mineralized tissue that can generally be categorized into two morphological groups: “cortical” bone and “cancellous” bone. Outer walls of all bones are composed of cortical bone, which has a dense, compact bone structure characterized by a microscopic porosity. Cancellous or “trabecular” bone forms the interior structure of bones. Cancellous bone is composed of a lattice of interconnected slender rods and plates known by the term “trabeculae.”

During certain bone procedures, cancellous bone is supplemented by an injection of a palliative (or curative) material employed to stabilize the trabeculae. For example, superior and inferior vertebrae in the spine can be beneficially stabilized by the injection of an appropriate, curable material (e.g., polymethylmethacrylate (PMMA) or other bone curable material). In other procedures, percutaneous injection under computed tomography (CT) and/or fluoroscopic guidance of stabilization material into vertebral compression fractures by, for example, transpedicular or parapedicular approaches, has proven beneficial in relieving pain and stabilizing damaged bone sites. Other skeletal bones (e.g., the femur) can be treated in a similar fashion. In any regard, bone in general, and cancellous bone in particular, can be strengthened and stabilized by a palliative injection of bone-compatible material.

Using a vertebropasty as a non-limiting example, a conventional technique for delivering the bone stabilizing material entails placing a cannula with an internal stylet into the desired injection site. The cannula and stylet are used in conjunction to pierce the cutaneous layers of a patient above the hard tissue to be supplemented, then to penetrate the hard cortical bone of the vertebra, and finally to traverse into the softer cancellous bone underlying the cortical bone. Once positioned in the cancellous bone, the stylet is then removed leaving the cannula in the appropriate position for delivery of curable material to the trabecular space of the vertebra to reinforce and solidify the damaged hard tissue.

According to one method in the prior art, curable material, is introduced into an end of the cannula for delivery into the vertebra using a 1 cc syringe. A 1 cc syringe is used because it generates the high pressures required to the force curable material through the cannula and into the vertebra. A disadvantage of a 1 cc syringe is that an amount of curable material required for the procedure is larger than 1 cc. As a result, it is required to sterilely reload the syringe several times during the procedure. This increases time and complexity of the procedure and increases the risk of radiation exposure to the physician.

An improved prior art procedure uses a curable material injector loaded with a relatively larger volume of curable material. The injector is connected to an end of the cannula via a non-compliant supply tube. Pressure created at the injector pushes a column of curable material through the supply tube and into the cannula. Curable material is then delivered from the cannula into the trabecular space of the vertebra. Although an improvement over the use of a syringe, the method has several disadvantages.

The method results in less control for the physician because the flow of curable material through the cannula has been found to be somewhat unpredictable. A column of curable material is pushed by substantial pressure over a distance, creating a pressure head in the column. When the curable material column reaches the end of the cannula, physicians have experienced that the curable material can burst into the trabecular space, depositing an uncontrolled volume of curable material in an uncontrolled manner. Further, the transfer of curable material from the injector to the vertebra can only begin after the supply tube is connected to the cannula. A significant amount of time can elapse while the column of curable material is advanced through the supply tube and cannula.

Moreover, during a long procedure, curable material can begin to solidify inside of the cannula. After the desired amount of curable material is deposited in the vertebra, the cannula is removed at the completion of the procedure. The curable material that was in the cannula that may have begun to set may remain attached to the core of curable material in the bone. As the cannula is removed, the curable material may break inside of the cannula instead of at the tip of the cannula and leave a “spike” of curable material protruding from the vertebra.

There exists a need in the medical device field for an improved subcutaneous bone material delivery system. The present invention provides an efficient device and method of introducing curable material, or other material, into a bone structure in a controlled manner.

BRIEF SUMMARY

One aspect of the present invention is directed to an apparatus for introducing material into an injection site of a patient. The apparatus includes a cannula defining a lumen. The apparatus also includes a carrier for delivering material from an injector to an injection site. The carrier defines a lumen and includes a supply section operable to receive curable material, and an inner section having an axis and defining a tip section operable to direct material in a direction that is not coaxial with the axis of the inner section. In the apparatus, the carrier is releasably attachable with the cannula, and at least a portion of the inner section is located within the lumen of the cannula.

In another aspect of the present invention, an apparatus is provided for introducing material into an injection site of a patient. The apparatus has an injector containing a volume of material, a cannula having an elongated portion defining a lumen wherein an end of the elongated portion is for positioning within the injection site and a carrier defining a lumen between the injector and the injection site. The carrier further includes a supply tube having a first end adaptable for connecting the supply tube with the injector and receiving material from the injector and a second end. The carrier also includes a connector attaching the carrier with the cannula. The connector also defines a chamber. The carrier also includes an inner tube having a first end and a second end, wherein the connector connects the second end of the supply tube with the first end of the inner tube via a chamber such that the supply tube, chamber and inner tube form a lumen having a substantially smooth transition from the supply tube to the inner tube. In the apparatus, at least a portion of the inner tube is located within the lumen of the elongated portion of the cannula.

In yet another aspect of the present invention, a method of delivering material to the injection site is provided. The method includes a step of inserting a cannula defining an elongated lumen into an injection site. The method also includes a step of connecting a carrier defining a lumen with an injector containing a volume of material. The method further includes a step of pre-loading the lumen of the carrier with the material so that the material is delivered to a distal end of the carrier from the injector, wherein the carrier is thus pre-loaded with material. The method also includes a step of inserting at least a portion of the distal end of the pre-loaded carrier into the elongated lumen of the cannula and delivering material to an injection site.

In another aspect of the present invention, a method of delivering material to the injection site is provided. The method includes a step of inserting a cannula defining an elongated lumen into an injection site. The method also includes a step of connecting a carrier with an injector containing a volume of material, said carrier defining a lumen and comprising an inner section distal from the injector. The method further includes a step of inserting at least a portion of the distal inner section of the carrier into the elongated lumen of the cannula. The method also includes a step of transmitting material from the injector through the lumen of the carrier wherein curable material is also transmitted through the distal inner section. The method finally includes a step of delivering material to an injection site.

Advantages of the present invention will become more apparent to those skilled in the art from the following description of the preferred embodiments of the invention which have been shown and described by way of illustration. As will be realized, the invention is capable of other and different embodiments, and its details are capable of modification in various respects. Accordingly, the drawings and description are to be regarded as illustrative in nature and not as restrictive.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of the curable material delivery device according to a preferred embodiment of the present invention prior to insertion of the inner section into the cannula;

FIG. 2 is a cross-section view of the curable material delivery device according to a preferred embodiment of the present invention after insertion of the inner section into the cannula;

FIG. 3 is a cross-section view of the curable material delivery device according to another preferred embodiment of the present invention after insertion of the inner tube into the cannula;

FIG. 4 is a cross-section of the connection between the supply tube and the cannula according to a preferred embodiment of the present invention;

FIG. 4 a is a cross-section of the inner section according to a preferred embodiment of the present invention;

FIG. 5 is a cross-section of the connection between the supply tube and the cannula according to a another preferred embodiment of the present invention;

FIG. 5 a is a cross-section view of the curable material delivery device according to another preferred embodiment of the present invention;

FIG. 5 b is a cross-section view of the curable material delivery device according to another preferred embodiment of the present invention;

FIG. 5 c is a cross-section view of the curable material delivery device according to another preferred embodiment of the present invention;

FIG. 6 is a perspective view of the curable material delivery device according to a preferred embodiment of the present invention after insertion of the inner section into the cannula;

FIG. 7 is a perspective view of the tip portion of the curable material delivery device according to a preferred embodiment of the present invention;

FIG. 8 is a perspective view of the tip portion of the curable material delivery device according to another preferred embodiment of the present invention;

FIG. 9 is a perspective view of the tip portion of the curable material delivery device according to another preferred embodiment of the present invention; and

FIG. 10 is a perspective view of the curable material delivery device according to a preferred embodiment of the present invention.

DETAILED DESCRIPTION OF THE DRAWINGS AND THE PRESENTLY PREFERRED EMBODIMENTS

FIG. 1 illustrates components of an intraosseous, curable material delivery system 5 according to principles of the present invention. The curable material delivery system 5 according to a preferred embodiment of the present invention has an injector 10, a carrier assembly 20 connected to the injector 10 via an injection connector 110 and a cannula 30 for insertion into a bone site of interest in a patient. In the embodiment depicted in FIG. 1, the bone site of interest is a vertebra 40.

Details on the various components are provided below. In general terms, however, a portion of the carrier assembly 20 is sized to be slidably disposed within the cannula 30 that otherwise serves to form and/or locate a desired injection site within a bone. Once positioned within the cannula, the carrier assembly 20 is employed to inject a curable, bone stabilizing material into the delivery site. The system 5 can be used for a number of different procedures, including, for example, vertebroplasty and other bone augmentation procedures in which curable material is delivered to a site within bone, as well as to remove or aspirate material from a site within bone.

The system 5, and in particular the carrier assembly 20, is highly useful for delivering a curable material in the form of a bone cement curable material. The phrase “curable material” within the context of the substance that can be delivered by the system/device of the invention described herein is intended to refer to materials (e.g., composites, polymers, and the like) that have a fluid or flowable state or phase and a hardened, solid or cured state or phase. Curable materials include, but are not limited to injectable bone cements (such as polymethylmethacrylate (PMMA) bone curable material), which have a flowable state wherein they can be delivered (e.g., injected) by a cannula to a site and subsequently cure into hardened curable material. Other materials, such as calcium phosphates, bone in-growth material, antibiotics, proteins, etc., could be used in place of or to augment, bone cement (but do not affect an overriding characteristic of the resultant formulation having a flowable state and a hardened, solid or cured state). This would allow the body to reabsorb the curable material or improve the clinical outcome based on the type of filler implant material.

The injector 10 may typically comprise a chamber filled with a volume of curable material and uses any suitable injection system or pumping mechanism to transmit curable material out of the injector and through the carrier assembly 20. Typically, a hand injection system is used where a physician applies force by hand to an injector. The force is then translated into pressure on the curable material to flow out of the chamber. A motorized system may also be used to apply force.

A cannula 30 is provided to be positioned in an injection site for delivery of curable material therein. The cannula 30 is preferably made of a surgical grade of stainless steel, but may be made of known equivalent materials which are both biocompatible and substantially non-compliant at operating pressures described herein. The cannula 30 defines a lumen 325 to allow the stylet (not shown), carrier assembly 20, and other equipment to pass through the cannula 30. Preferably, at least a distal end 330 of the cannula 30 is radiopaque. The cannula 30 has an inside diameter which is only slightly larger than the outside diameter of the stylet. The distal end 330 of the cannula 30 is preferably beveled to ease the penetration of the cannula through the cutaneous and soft tissues, and especially through the hard tissues.

Surrounding the proximal end 328 of the cannula 30 is a handle 310 for manipulating the cannula 30 and connecting the cannula 30 with carrier assembly 20 via a handle connector 312. Preferably, handle connector 312 has a Luer-lock type of connector, but other known connecting mechanisms may be successfully interchanged, e.g., a conventional threaded hole, a thread and locking nut arrangement, etc. Cannulas may be of standard lengths and diameters. A cannula may be about 4 cm to about 20 cm long and is preferably 12 cm long. Additionally, with respect to the cannula diameter, the cannula may be about 1.2 mm in outer diameter (18 gauge) with a wall thickness of about 0.216 mm to about 5.2 mm in outer diameter (6 gauge) with a wall thickness of about 0.381 mm, and is preferably about 3.1 mm in outer diameter (11 gauge) with a wall thickness of about 0.33 mm or about 2.1 mm in outer diameter (13 gauge) with a wall thickness of about 0.305 mm.

The carrier assembly 20 provides a passageway for curable material to travel from the injector 10 to an injection site, such as a vertebra 40. With reference to FIG. 2, carrier assembly 20 preferably defines a lumen 100 from the injection connector 110 to its terminal end 144 positioned inside of a patient. According to one preferred embodiment, the carrier assembly 20 comprises an injection connector 110, a cannula connector 130 and a transfer body 115. The transfer body 115 further comprises a supply section 120 and an inner section 140. The injection connector 110 is preferably a Luer-lock type of connector, but other known connecting mechanisms suitable for medical applications may be successfully interchanged.

The cannula connector 130 is fixedly attached to the transfer body 115 and connects the carrier assembly 20 with the cannula 30 and cannula handle 310. According to a preferred embodiment, the cannula connector 130 contains a Luer-lock threaded fitting 200 for connection with a Luer-lock threaded fitting 300 of the cannula 30 to allow the carrier assembly 20 and cannula 30 to be removably detachable.

The transfer body 115 is preferably a single tubular structure that defines lumen 100. Due to the operating pressures required to transfer curable material through the carrier assembly 20, the transfer body 115 is preferably made of a non-compliant material such as polyetheretherketone (PEEK). Other suitable materials include aluminum or wire reinforced plastic. The supply section 120 of the transfer body 115 is operable to receive curable material from the injector 10 and is generally defined by the section of the transfer body 115 between the injector 10 and the cannula connector 130. The inner section 120 of the transfer body 115 is operable to deliver curable material to an injection site and is generally defined by the section of the transfer body 115 between the cannula connector 130 and the terminal end 144 of the carrier assembly 20 for positioning within the patient. At least a portion of the inner section 140 is adapted to be inserted into the cannula 30. The inner section 140 must therefore have an outer diameter that is smaller than the inner diameter of the cannula 30; however, the outer diameter should not be so small so as to allow curable material to travel around the outside of the inner section 140 and back into the cannula 30. Preferably the clearance between the inner diameter of the cannula 30 and the outer diameter of the inner section 140 is within a range of about 1 to 30 thousandths of an inch and is more preferably no more than about 5 thousands of an inch.

Additionally, according to a preferred embodiment the distal end 330 of the cannula 30 extends beyond the terminal end 144 of the inner section 140 such that the terminal end 144 of the inner section 140 is at a length from the distal end 330 of the cannula 30 that is less than 50% of the length of the cannula 30. According to another preferred embodiment, the terminal end 144 of the inner section 140 is substantially even with the distal end 330 of the cannula 30. One skilled in the art will also understand that an inner section 140 that extends beyond the distal end 330 of the cannula 30 may also be used as long as the inner section 140 fits within the injection site and dispenses curable material effectively.

One skilled in the art will appreciate that although this embodiment uses a single tube for delivering curable material to the patient, the single tube may be manufactured to have different diameters at different sections of the tube.

With reference to FIG. 3, in another preferred embodiment, the supply section 120 and inner section 140 may be separate structures that are connected at the cannula connector 130. In this embodiment, preferably the supply section 120, cannula connector 130 and inner section 140 define the lumen 100. The supply section 120 has a first end 122 and second end 124 and is preferably a tubular structure that defines a portion of the lumen 100. Due to the operating pressures required to transfer curable material through the carrier assembly 20, the supply section 120 is preferably made of a non-compliant material such as polyetheretherketone (PEEK) or other polymer. Other suitable materials include aluminum or wire reinforced plastic. The second end 124 of the supply section 120 connects with a first end 132 of the cannula connector 130.

The inner section 140 comprises a first end 142 connected with the cannula connector 130 and a terminal end 144 for positioning within the patient to deliver curable material to an injection site. The inner section 140 is adapted to be inserted into the cannula and preferably extends from the cannula connector 130 to the injection site. Due to the operational pressures applied with injecting curable material, the inner section 140 is preferable made of a non-compliant material and is more preferably made of polyetheretherketone (PEEK) or aluminum. The inner section 140 must therefore have an outer diameter that is smaller than the inner diameter of the cannula 30; however, the outer diameter should not be so small so as to allow curable material to travel around the outside of the inner section 140 and back into the cannula 30. Preferably the clearance between the inner diameter of the cannula 30 and the outer diameter of the inner section 140 is within a range of about 1 to 30 thousandths of an inch and is more preferably no more than about 5 thousands of an inch. The supply section 120 and the inner section 140 may be made of the same or different materials.

According to one preferred embodiment of the inner section 140, the interior surface of the inner section 140 is smooth to aid in delivery of material to a delivery site. Typical medical cannulas or needles in the prior art for introducing curable material contain rough inner surfaces. Rough inner surfaces may have root-mean-square (RMS) values of 50 micro inches and greater, and some smooth surfaces may have RMS values of less than 50. It has been observed that the application of curable material requires relatively less force when the surfaces defining the lumen for introducing the curable material are smooth. Smooth surfaces may have root-mean-square (RMS) values of about 45 and lower. As a result, in a preferred embodiment, the RMS value of the inner section defining lumen 100 has an RMS value of between about 0 and about 45. In another preferred embodiment, the RMS value is preferably between about 0 and about 32, and is more preferably between about 0 and about 16.

FIG. 4 a depicts an inner section 140 having a smooth interior surface 141 defining a portion of lumen 100. In one preferred embodiment, the interior surface 141 of the inner section 140 is coated with a dry lubricant, which may include a coating such as polytetrafluoroethylene (PTFE) (e.g., Teflon®). In another preferred embodiment, a smooth-surface liner having a smooth interior surface 141 may be placed within the inner section 140 such the smooth-surface liner covers the interior surface of the inner section 140. According to one preferred embodiment, the smooth-surface liner is made of Teflon®. In another preferred embodiment, the interior surface 141 of inner section 140 is manufactured to have a polished or mirror surface finish such that the interior surface 141 of the inner section 140 has a substantially smooth surface finish having an RMS value of 45 or lower. In this embodiment, the inner section 140 is preferably made of metal and is more preferably made of stainless steel.

Additionally, according to a preferred embodiment the distal end 330 of the cannula 30 extends beyond the terminal end 144 of the inner section 140 such that the terminal end 144 of the inner section 140 is at a length from the distal end 330 of the cannula 30 that is less than 50% of the length of the cannula 30. According to another preferred embodiment, the terminal end 144 of the inner section 140 is substantially even with the distal end 330 of the cannula 30. One skilled in the art will also understand that an inner section 140 that extends beyond the distal end 330 of the cannula 30 may also be used as long as the inner section 140 fits within the injection site and dispenses curable material effectively.

In this embodiment, in addition to connecting the carrier assembly 20 with the cannula 30, the cannula connector 130 also connects the supply section 120 with the inner section 140. According to a preferred embodiment, the supply tube 120 connects with the cannula connector 130 via a Luer-lock type of connector 210, but other known connecting mechanisms suitable for medical applications may be successfully interchanged. The cannula connector 130 further comprises a second Luer connection 312 for connecting the inner section 140 with the cannula connector 130.

With reference to FIG. 4, the cannula connector 130 preferably comprises a flangeless adapter 220. Flangeless adapter 220 provides a precise and smooth transition from the supply section 120 to the inner section 140. It has been found that disruptions in the walls defining the lumen 100, such as at abrupt transitions in fittings or connections, can cause curable material within the lumen 100 to prematurely set and potentially plug the line. As a result, a smooth transition at fittings or connections between lines advantageously delivers curable material to the patient.

Preferably, flangeless adapter 220 defines a first radial lip 230, a chamber 240, and a second radial lip 250. The chamber 240 further defines an input end 242, an output end 244 and a transition region 246. To effect a precise and smooth transition from the supply section 120 to the chamber 240, the second end of the supply section 124 abuts with the first radial lip 230 at the input end 242 of the chamber 240. The input end 242 of the chamber has an inner diameter that is substantially the same inner diameter of the supply section 120. Similarly, the first end 142 of the inner section 140 abuts with the second radial lip 250 at the output end 244 of the chamber 240. The output end 244 of the chamber 240 has an inner diameter that that is substantially the same as the inner diameter of the inner section 140. It will thus be appreciated that a precise and smooth transition between the supply section and the inner section is achieved.

In the embodiment depicted in FIG. 4, the supply section 120 and the inner section 140 have the same inner diameter. As a result the input end 242, transition region 246 and output end 244 of the chamber also have the same diameter. In another preferred embodiment, the supply section 120 and the inner section 140 may have different inner diameters. Accordingly, the input end 242 and output end 244 of the chamber 240 will also have different inner diameters. In this embodiment, the transition region 246 of the chamber 240 is tapered to smoothly transition the chamber 240 from one diameter to the other.

It has been observed that the application of curable material is more controllable where the downstream pathway of the curable material is narrower than the upstream pathway. As a result, according to a preferred embodiment, the inner diameter of the inner section 140 is smaller than the inner diameter of the supply section 120. In this preferred embodiment, the transition region 246 will preferably smoothly transition the chamber 240 from a larger diameter at the input end 242 of the chamber to a smaller diameter at the output end 244 of the chamber. It is important to keep in mind that abrupt transitions in connections should be avoided to prevent plugging by the curable material. The flangeless adapter 220 is preferably made of a material that can withstand the operational pressures such as polyetheretherketone (PEEK) or other polymers.

With reference to FIG. 5, another embodiment of the cannula connector is presented. In this embodiment the supply section 120 and the inner section 140 are conveniently detachable from each other such that different inner sections 140 may be attached and detached from the supply section 120. In this embodiment, the inner section 140 comprises an inner section connector 480. The inner section connector 480 connects with the cannula connector 130 via the Luer-lock connection 200 that was used to connect to the cannula handle 310 in the previous embodiment. The inner section connector 480 also comprises another Luer-lock connection 475 for connection to the cannula handle 310. The inner section connector 480 further comprises a second flangeless adapter 420 to provide a precise and smooth transition from the cannula connector 130 to the inner section 140. With reference to FIG. 5, preferably the second flangeless adapter 420 defines a chamber 440 and a radial lip 450. The chamber 440 further defines an input end 442, an output end 444 and a transition region 446. To effect a precise and smooth transition from the cannula connector 130 to the chamber 440, the output end 477 of the chamber 240 of the cannula connector 130 abuts with the input end 442 of the second chamber 440. The input end 442 of the second chamber 440 has an inner diameter that is substantially the same inner diameter of the output end 477 of the chamber 240 of the cannula connector 130. It will be appreciated that multiple sizes of inner sections may be attached to a single sized supply section because each inner section connector contains a particularly tapered transition region 446 that is suitable to smoothly transition the supply section 120 with an inner section 140.

With reference to FIG. 5 a, another embodiment of the cannula connector is presented. In this embodiment the supply section 120 (not shown) and the inner section 140 are conveniently detachable from each other such that different inner sections 140 may be attached and detached from the supply section 120. Additionally, in this embodiment the supply section 120 is conveniently rotatable with respect to the inner section 140 such that the material injector and supply section 140 may be rotated around the longitudinal axis of the inner section 140 to achieve a preferred orientation for ease of use. In this embodiment, the inner section 140 is connected with a connector body 680. The connector body 680 connects via a Luer-lock connection 682 to the cannula handle 310 (see FIG. 1). The connector body 680 also comprises fixed adapter 690 and a rotating adapter 620. The rotating adapter 620 allows a rotatable transition from the supply section 120 to the inner section 140 via the connecter body 680. In this embodiment, the rotating adapter 620 is operative to rotate with respect to the fixed adapter 690 and to rotate about the longitudinal axis of the inner section 140. The rotating adapter 620 is operative to interface with the supply section 120 and allow the supply section 120 to rotate during use. In a preferred embodiment, the rotating adapter is operative to rotate the supply section preferably about 90 degrees and more preferably about 360 degrees.

With reference to FIG. 5 a, according to one preferred embodiment the rotating adapter 620 defines a grip section 622, a holder section 624 and a cap 626. In one preferred embodiment the grip section 622 and holder section 624 are connected with each other by an adhesive; however, in another embodiment, the grip and holder sections may be integrally formed. The holder 624 section is inserted into a cavity in the fixed adapter 690 and the cap 626 is placed over the end of the fixed adapter 690 to secure the holder section 624 within the fixed adapter 690. According to one preferred embodiment, the cavity of the fixed adapter 690 also contains an O-ring 692 to interface with the holder section 624. The grip section 622 preferably contains one or more fin-like projections 630 to aid in rotating the rotating adapter 620. The grip section 622 also contains a Luer threading 628 operative to connect the supply section 120 to the connecter body 680. When assembled, the connecter body 680, inner section 140 and supply section 120 form a lumen to allow material to be delivered from the material injector to the material delivery site.

In another embodiment of the connector body 680, connector body 680 further comprises a flangeless adapter (not shown) in accordance with the flangeless adapters described herein to provide a precise and smooth transition from the supply section 120 to the inner section 140. It will also be appreciated that because the inner section is detachable from the supply section, multiple sizes of inner sections may be attached to a single sized supply section.

According to another preferred embodiment, the inner section 140 also rotates as the rotating adapter 620 is rotated. In this embodiment, rotation of the supply section 120 causes the inner section 140 to rotate to provide for directional delivery of curable material within the injection site. With reference to FIG. 5 b, according to one preferred embodiment the inner section 140 is connected to the rotating adapter 620. As can be seen in FIG. 5 b, the inner section 140 extends through the fixed adapter 680 to the rotating adapter 620. The inner section 140 and rotating adapter 620 may be connected by an adhesive; however, other connection means may be used. According to one preferred embodiment, an end 691 of the inner section 140 may be flared to correspond with a surface of the rotating adapter 620 to aid in manufacturing of the invention and to increase surface area for an adhesive. In this embodiment, the supply section 120 is connected with the rotating adapter as described above. As the supply section is rotated about the longitudinal axis of the inner section 140, the inner section is also rotated within and relative to the fixed adapter 690. Thus, rotation of the inner section 140 is dependant on rotation of the supply section. When used with various inner section tip configurations, rotation of the supply section will cause rotation of inner section and provide for directional application of curable material within the injection site.

According to yet another preferred embodiment, the inner section 140 and the supply section 140 can rotate independently of each other. In this embodiment, the supply section 120 may be rotated about the longitudinal axis of the inner section 140 without causing the inner section 140 to rotate. Additionally, the inner section 140 may be rotated to provide directional cement delivery without rotating the supply section 120. With reference to FIG. 5 c, in this embodiment rotating adapter 620 is connected with a second connector body 780. The second connector body 780 connects to the rotating adapter 620 via Luer thread 628. The second connector body 780 also comprises a second fixed adapter 790 and a second rotating adapter 720. The second rotating adapter 720 allows an independent rotatable transition from the supply section 120 to the inner section 140. In this embodiment, the second rotating adapter 720 is operative to rotate with respect to the second fixed adapter 790 and to rotate about the longitudinal axis of the inner section 140. The second rotating adapter 720 is operative to interface with the supply section 120 and allow the supply section 120 to rotate during use.

With continued reference to FIG. 5 c, according to one preferred embodiment the second rotating adapter 720 defines a second grip section 722, a second holder section 724 and a second cap 726. In one preferred embodiment the second grip section 722 and second holder section 724 are connected with each other by an adhesive; however, in another embodiment, the grip and holder sections may be integrally formed. The second holder section 724 is inserted into a cavity in the second fixed adapter 790 and the second cap 726 is placed over the end of the second fixed adapter 790 to secure the second holder section 724 within the second fixed adapter 790. According to one preferred embodiment, the cavity of the fixed adapter 690 also contains a second O-ring 792 to interface with the second holder section 724. The second grip section 622 preferably contains one or more fin-like projections 730 to aid in rotating the second rotating adapter 720. The second grip section 722 also contains a Luer threading 728 operative to connect the supply section 120 to the second connecter body 780. When assembled, the connecter body 680, second connecter body 780, inner section 140 and supply section 120 form a lumen to allow material to be delivered from the material injector to the material delivery site.

In this embodiment, the inner section 140 may be rotated using the rotating adapter 620 independently of rotation of the supply section 120. When used with various inner section tip configurations, rotation of the inner section 140 will provide for directional application of curable material within the injection site.

Regardless of an exact configuration, the assembled curable material delivery system (such as the curable material delivery system 5 of FIG. 1) in accordance with principles of the present invention is highly useful in performing a wide variety of bone stabilizing procedures as part of an overall curable material delivery system. Using a vertebroplasty as a non-limiting example, in operation, the cannula 30 and stylet (not shown) are driven into the vertebra 40 to reach the trabecular cavity of the vertebra 40. The stylet is removed, leaving an open lumen 325 within the cannula 30. Curable material is mixed and loaded into the injector 10. Preferably, curable material is transferred under pressure from the injector 10 to the terminal end 144 of the inner section 140 prior to insertion of the inner section 140 into the lumen 325 of the cannula 30. In practice, an operator may advance curable material beyond the terminal end 144 of the inner section 140 in order to completely fill the inner section 140 and then wipe the terminal end 144 of the inner section 140 of excess curable material before insertion into the cannula 30. The carrier assembly is thus preloaded with curable material before the carrier assembly 20 is connected with the cannula 30 and the inner section 140 is inserted into the cannula 30. Once the inner section 140 is inserted into the cannula 30 and the carrier assembly 20 is connected with the cannula 30, curable material is immediately available to be delivered into the vertebra 40. This preloading step advantageously reduces the time required to deliver curable material into a patient because it can be done at substantially the same time the cannula 30 is being driven into the vertebra. In the prior art, the transfer of curable material from the injector can begin only after a supply tube is connected with the cannula. Time is thus required to transfer curable material from the injector to the supply tube, through the cannula tube, and into the patient. In the preferred embodiment of the present invention, however, curable material is preloaded to the terminal end 144 of the inner section 140 and the inner section 140 is then inserted into the cannula 30, thus making curable material immediately available to be delivered to the patient. One skilled in the art will realize, however, that curable material need not be preloaded into the carrier assembly to realize other advantages on the present invention.

It has been observed that during the initial preloading of the delivery device with curable material, a “dry plug” forms at the end of the curable material column as it advances through the device. The dry plug is formed when monomer is extracted from the leading end of the column of curable material as it coats the inner surface of the delivery device lumen. As monomer is extracted from the curable material the end of the column becomes dry and increases friction against the inner surface. The dry plug becomes longer as the column of curable material is advanced which, in turn, further increases friction.

The dry plug thus requires the injector to exert greater pressure to advance the column of curable material when compared with a column that does not have a dry plug. As a result, according to one preferred embodiment a preferred method may be employed to reduce the effects of the dry plug during preloading. According to this preferred method of preloading the curable material delivery device, the inner section 140 is detached from the supply section 120 and curable material is loaded to the distal end of the supply section 120. The curable material is then further advanced so that the dry plug is dispelled from the distal end of the supply section 120. The distal end of the supply section 120 is then wiped clean of any excess curable material and the inner section 140 is attached to the supply section 120. Preloading of the curable material continues as described above.

At this point in the procedure, the inner section 140 is inserted into the cannula 30 and locked into place with the Luer-lock that connects the carrier assembly 20 to the cannula 30 in order to prohibit ejection of the carrier assembly 20 from the cannula 30 under pressure. The present invention permits burst-free injection of the curable material into an injection site at the beginning of the procedure because the carrier assembly 20 is primed prior to insertion into the cannula 30. When the physician activates the injector 10, the curable material is already going into the injection site and hence the flow is more predictable. The injector will then allow transfer of finely controlled amounts of curable material into the patient.

Following the delivery of a predetermined amount of curable material into the vertebra, the carrier assembly 20 may be detached from the cannula 30 and removed. It will be appreciated by one skilled in the art that when the carrier assembly 20 is removed, the inner section 140, which is loaded with curable material, is also removed and thus removes the column of curable material from the cannula 30. Several advantages are therefore realized in this embodiment. First, because the inner section 140 functions as a liner between the curable material and the cannula 30, there is no residual curable material inside of the cannula 30. The cannula 30 may therefore again be used to deliver additional material to the vertebra. Second, in the prior art, curable material may begin to set within the cannula 30 before completion of the procedure. When the procedure is complete and the cannula is removed, the resulting curable material column may break at a point inside the cannula 30 and not at the tip of the distal end 330 of the cannula 30. This results in a “spike” of curable material that is still attached to the curable material that has been deposited inside of the vertebra and the “spike” may extend outside of the vertebra. In the present invention, it has been observed that the curable material more uniformly breaks at the tip of the terminal end 144 of the inner section 140 when the inner section 140 is removed, thus minimizing the opportunities for curable material “spikes.” Additionally, it is understood in the art that curable material will begin to set more quickly when exposed to body temperature. In the present invention, if delivery of curable material needs to be interrupted for a period of time, the inner section 140 can be conveniently temporarily removed from the cannula 30 and cooled by the relatively cooler room temperature, slowing the setting of the curable material. This is not possible under the prior art where curable material filled within the cannula 30 cannot be removed during the operation.

The present invention also allows a physician to conveniently fill multiple cannulas in one or more vertebra with curable material in the same operation. It is understood that a physician may enter a vertebral body with two basic approaches: uni-pedicular and bi-pedicular. In the uni-pedicular approach, the physician attempts to place the cannula in such a way that it traverses the midline of the vertebral body. This is done so that the entire vertebra can be filled through one entry point and one cannula. This technique can provide faster curable material filling, thus reducing procedure time. The technique, however, can be technically more challenging for the physician and may not always be possible to use. The bi-pedicular approach relies on placing a cannula through each pedicle of a vertebra. Because there is no need to traverse the midline of the vertebral body, the bi-pedicular approach is considered technically easier and safer. It permits equal filling on both sides of the vertebra, thus providing more uniform distribution of curable material.

The present invention can be used with both the uni-pedicular and bi-pedicular approaches. In the bipedicular approach the same carrier assembly 20 can be used to fill a first side of a vertebral body through a first cannula until the first side is satisfactorily filled. The inner section 140 of the carrier assembly 20 can then be removed from the first cannula and positioned within a second cannula to the other side of the vertebral body. It will be appreciated that upon removal of the carrier assembly 20, the first cannula is substantially free of curable material. It will also be appreciated that the inner section 140 is still filled with curable material and is thus “preloaded” with respect to the second procedure. Filling of the second side of the vertebral body can therefore immediately begin while the curable material begins to set on the first side. If the physician so desires, he or she can return to the first cannula and resume filling the first side. In a preferred embodiment, the physician can alternate between first and second cannula in a procedure, keeping both clean.

In another preferred embodiment, the physician may fill two different vertebral bodies in one procedure. The technique allows the physician to work between cannulas at various times while keeping the cannulas clean. In this embodiment, the physician drives cannulas into two or more vertebra. The carrier assembly 20 is preloaded with curable material as described above. The carrier assembly 20 is connected with the first cannula 30 for the first procedure and curable material is immediately delivered to the vertebra. At the completion of the first procedure, the carrier assembly 20 is removed from the first cannula 30. It will be appreciated that the inner section 140 is still filled with curable material and is thus “preloaded” with respect to the second procedure. The carrier assembly 20 is connected to the second cannula 30 and curable material is ready to be immediately delivered to the vertebra.

Alternative structures may be employed within the scope of the present invention. With reference to FIG. 6, in another preferred embodiment, the terminal end 144 of the inner section extends beyond the distal end 330 of the cannula 30. The tip portion 550 of the terminal end 144 can contain different configurations to deliver curable material to an injection site.

In a preferred embodiment shown in FIG. 7, the tip portion 550 contains a closed, blunt end 518 such that the terminal end 144 is axially closed to the lumen 100 (i.e., material cannot be axially expelled from the terminal end 144 relative to an axis of the lumen 100). That is to say, material in the lumen 100 cannot be forced distally therefrom in an axial fashion. Further, the terminal end 100 defines or includes a blunt end 518. In one embodiment, the blunt end 518 defines a hemispherical surface, although other blunt (i.e., curved or curvilinear) shapes or contours are also acceptable. The blunt end 518 is adapted to provide a non-traumatic surface suitable for accessing, contacting and probing bone or tissue while minimizing the risk of puncture and/or coring of the tissue or damage to the bone.

The tip portion 550 also defines a side orifice 520 formed adjacent the terminal end 144, extending through a thickness of a sidewall of the tip portion 550. The side orifice 520 can assume a wide variety of shapes and sizes. For example, the side orifice 520 can be oval, circular, curvilinear, etc. In one embodiment, a chamfered region 570 can be formed about the side orifice 520 to eliminate sharp edges along an exterior of the tip portion 550 as well as to promote consistent flow of curable material from the side orifice 520 (via the expanding orifice size effectuated by the chamfered region 570). Although the tip portion 550 has been described as including or otherwise forming one side orifice 520, two, circumferentially aligned side orifices can be provided

With reference to FIGS. 8-9, a variety of other configurations for the tip portion 550 are also acceptable. FIG. 8 shows a tip portion 550 having three side orifices 522 having consecutively smaller side orifices. This reduction in side orifice size proximal the terminal end 144 promotes consistent distribution of curable material otherwise being forced through the tip portion 550. While three of the side orifices 522 are shown, other configurations are also acceptable. For example, multiple side orifices (i.e., more than three side orifices) can be formed longitudinally along the length of the tip portion 550, and in addition, the side orifices can include more than one longitudinally aligned series of side orifices. In an exemplary embodiment, the side orifices that are visible in FIG. 8 are matched by another column of longitudinally aligned side orifices formed on an opposing side of the tip portion 550 (and therefore not visible in the view of FIG. 8). Aspects of the present invention provide for the side orifices 522 to define circular side orifices, non-circular side orifices, or a set of circular and non-circular side orifices.

FIG. 9 shows another preferred embodiment of the tip portion 550. In this embodiment, the tip portion 550 is bent to provide about a 90 degree opening 560 with respect to the axis of the inner section 140. In the exemplary embodiment, the angle between the opening 560 and the axis of the inner section, represented by θ, is 90 degrees. Aspects of the present invention contemplate that the angle θ may be between 0 and 90 degrees and are preferably substantially 90 degrees. Preferably, the leading edge of the tip portion 550 should be substantially rounded so that the tip portion 550 does not easily cut into tissue. In one embodiment, the inner section comprises a rotatable hub that rotates the inner section 140. The hub would comprise a visual indicator corresponding to the orientation of the opening 560 so that the clinician may visualize the opening at the terminal end of the inner section. Preferably, the hub of the inner section has a seal to allow the hub to be rotated 360 degrees. Therefore, the clinician can orient cement injection in any direction based upon the architecture of the area that the bone cement in injected into.

With reference to FIG. 10, another preferred embodiment of the present invention comprises a curved portion 510 at the terminal end 505 of the inner section that extends beyond the distal end of the cannula 30 during a procedure. In this embodiment, the curved portion 510 is a resilient preformed curved section capable of being straightened for insertion through the elongated tubular portion of the cannula. The curved portion also has a shape memory feature which allows it to return to its curved shape after exiting the distal end of the elongated tubular portion. The curved portion 510 may be formed integrally with the inner section or may be a separate structure that is bonded with the inner section. In a preferred embodiment, a visual indicator, such as a symbol or color indicator on the cannula connector, for example, is provided to indicate to the physician the orientation of the curved portion 510 relative to the cannula connector. The inner section 140 includes indicia 517 adjacent the terminal end 144. The indicia 517 are indicative of a location of the terminal end 144 relative to the distal end of the cannula 30. The indicia 517 can assume a wide variety of forms differing from that shown in FIG. 10, and in some embodiments can be eliminated. The end portion 550 may be any of the tip configurations described above.

In operation, a cannula is positioned within a vertebral body as described above. The carrier assembly having the curved portion 510 is preloaded with curable material and inserted into the elongated tubular portion of the cannula. Depth indicia 517 on the inner section may be used by the physician to determine how far the curved portion 510 has traveled beyond the distal end of the cannula 30. After the desired depth is achieved, curable material may be delivered to the vertebral body. Using the visual indicator of the orientation of the curved portion 517, the curved portion 515 may be repositioned so that curable material may be delivered to different areas within the vertebral body. Following the delivery of a predetermined amount of curable material into the vertebra, the carrier assembly 20 is removed from the cannula 30.

It is also contemplated that according to another preferred embodiment, the invention may be used with a tamping operation using an inflatable device. Tamping operations using a balloon are known in the prior art and are disclosed at, for example, U.S. Pat. No. 4,969,888, titled “Surgical Protocol for Fixation of Osteoporotic Bone Using Inflatable Device” and U.S. Pat. No. 5,108,404, titled “Surgical Protocol For Fixation of Bone Using Inflatable Device.” In those procedures in which physicians believe a clinical advantage can be gained by tamping the internal bone, the present invention may be used in the following manner. First, a physician gains entry into the bone using a cannula and stylet combination. After gaining entry, the trabecular bone is morcellated to create a void for the tamping device. The tamping device is inserted into this space and expanded, thus enlarging the void in the bone. After the tamping device is removed, the preloaded inner section is inserted into the cannula and curable material is delivered into the site as already described.

It is therefore intended that the foregoing detailed description be regarded as illustrative rather than limiting, and that it be understood that it is the following claims, including all equivalents, that are intended to define the spirit and scope of this invention. In this regard, it should be understood that although reference to bone sites and curable material has been made, the devices and methods disclosed herein are not limited in application to bone sites and curable materials. One skilled in the art will understand that the devices and methods disclosed herein may be used at non-bone sites such as spinal discs and may be used to inject material other than curable material.

INDUSTRIAL APPLICABILITY

The system and method answers a long felt need for increasing safety and control in the administration of curable material to a bone site by providing an inner section of tubing within a cannula that may be preloaded with curable material. The inner section of tubing allows a cannula to remain free of the curable material so that it may be reused during the procedure. Additionally, preloading the inner section of tubing with curable material allows for reduced time to deliver curable material to a patient and increases control over the curable material delivery. 

1. An apparatus configured for introducing material into an injection site of a patient comprising: a tubular section having an interior surface defining a lumen for transporting curable material wherein the interior surface of the lumen is smooth, having an RMS value less than
 50. 2. The apparatus of claim 1 wherein the smooth interior surface has an RMS value of about 0 to about
 45. 3. The apparatus of claim 1 wherein the smooth interior surface has an RMS value of about 0 to about
 36. 4. The apparatus of claim 1 wherein the interior surface has an RMS value of about 0 to about
 16. 5. The apparatus of claim 1 wherein the interior surface is coated with a dry lubricant.
 6. The apparatus of claim 5 wherein the dry lubricant comprises PTFE.
 7. The apparatus of claim 1 wherein a liner within the tubular section defines the smooth interior surface.
 8. The apparatus of claim 7 wherein the liner is made of Teflon®.
 9. The apparatus of claim 1 wherein the tubular section is metallic.
 10. The apparatus of claim 1 further comprising a cannula defining a cannula lumen wherein at least a portion of the tubular section is configured to be located within the cannula lumen during delivery of the material.
 11. An apparatus according to claim 10 and further comprising: a carrier for delivering material from an injector to an injection site, the carrier defining a lumen and the carrier comprising a supply section operable to receive curable material, and the tubular section configured as an inner section having a longitudinal axis, wherein the supply section is rotatable with respect to the longitudinal axis of the inner section and at least a portion of the inner section is located within the cannula lumen.
 12. The apparatus of claim 11 wherein the inner section is rotatable and rotation of the inner section is dependent on rotation of the supply section.
 13. The apparatus of claim 11 wherein the inner section is rotatable and rotation of the inner section is independent of rotation of the supply section.
 14. The apparatus of claim 11 wherein the carrier further comprises a connector for connecting an end of the supply section with an end of the inner section wherein the connector defines a chamber between the end of the supply section and the end of the inner section.
 15. The apparatus of claim 14 wherein the connector further comprises a rotating adapter that connects with the end of the supply section.
 16. The apparatus of claim 15 wherein the rotating adapter is operative to rotate the supply section at least about 90 degrees.
 17. The apparatus of claim 16 wherein the supply section, chamber and inner section form a lumen having walls defining a substantially smooth transition from the supply section to the inner section.
 18. A method of delivering material to an injection site comprising the steps of: providing an apparatus according to claim 1, wherein the supply section is configured as a tubular supply section defining a supply section lumen; inserting the cannula into an injection site; connecting the tubular supply section with an injector containing a volume of material; advancing material through the tubular supply section lumen from the injector a sufficient distance to dispel a dry plug of material from the tubular supply section; connecting the tubular inner section of the carrier with the supply section; pre-loading the lumen of the carrier with the material so that the material is delivered to a distal end of the tubular inner section from the injector, wherein the carrier is thereby pre-loaded with material; inserting at least a portion of the distal end of the pre-loaded tubular inner section into the elongated lumen of the cannula; and delivering material to an injection site.
 19. The method of claim 18 wherein the injection site and a second injection site are within a vertebra.
 20. The method of claim 19 wherein the tubular supply section and the tubular inner section are of different diameters. 